Biohybrid Composite Scaffold

ABSTRACT

A biohybrid scaffold is provided that is useful in clinical applications for abdominal wall reconstruction, pelvic floor repair, breast reconstruction, as well as other soft tissue repairs. Methods of making and using the biohybrid scaffold are provided.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a Divisional of U.S. patent application Ser. No.13/814,783, which is a National Stage of International PatentApplication No. PCT/US2011/048071, filed Aug. 17, 2011, which claims thebenefit of U.S. Provisional Patent Application No. 61/374,340, filedAug. 17, 2010, each of which is herein incorporated by reference in itsentirety.

STATEMENT REGARDING FEDERAL FUNDING

This invention was made with government support under Grant No.W81XWH-08-2-0032 awarded by the Army/MRMC. The government has certainrights in the invention.

Biologic scaffolds composed of extracellular matrix (ECM) are utilizedin numerous regenerative medicine applications to facilitate theconstructive remodeling of tissues and organs. The mechanisms by whichthe host remodeling response occurs are not fully understood, but recentstudies suggest that both constituent growth factors and biologicallyactive degradation products derived from ECM play important roles.

The extracellular matrix (ECM) represents the secreted product ofresident cells within every tissue and organ and thus defines apreferred collection of structural and functional molecules best suitedto support the viability and phenotype of those cells. The ECM is in astate of dynamic reciprocity with the cells of each tissue, and thegrowth factors, cytokines, chemokines, and other signaling moleculeswithin the ECM play important roles in development, homeostasis, andresponse to injury. A variety of mammalian tissues and organs, includingthe small intestine, liver, urinary bladder, arterial vasculature, heartvalves, and dermis, have been decellularized, and the remaining ECM usedas a biologic scaffold to support the reconstruction of injured ormissing tissues. The mechanisms by which these biologic scaffoldsfacilitate tissue remodeling include both contact guidance and molecularsignaling, but the temporal and spatial patterns of these events remainlargely unknown.

SUMMARY

A novel biohybrid scaffold is generated here by concurrent extracellularmatrix (ECM) gel electrospraying and biodegradable elastomerelectrospinning. ECM gel possesses good bioactivity andbiocompatibility, but its weak mechanic properties and fast degradationlimits its clinical applications. Biodegradable elastomer can beprocessed into the sub-micro fibrous scaffold using electrospinning.This electrospun scaffold has attractive mechanical behaviors and goodcytocompatibility, however, it exhibits poor cellular penetration andtissue integration due to its dense structure, which would delay thetissue formation and healing. A biohybrid elastic scaffold is thereforeprovided which is fabricated by concurrent electrospray/electrospinning,and comprises interpenetrated ECM gel and elastomer fibers, where ECMgel would make the electrospun scaffold looser and provide thebioactivity and biocompatibility to accelerate cellular and tissueintegration and growth, while the elastomeric polymer fibers improve themechanical properties of the scaffold structure. The elastic biohybridscaffold is useful for clinical applications in tissue repair andreplacement.

According to one embodiment, a concurrent gel electrospray/polymerelectrospinning method is provided to obtain a biohybrid composite ofextracellular matrix (ECM) gel/biodegradable elastomeric fibers. Themethod comprises electrospinning a biodegradable, biocompatible,elastomeric polymer composition onto a substrate and concurrently orsubstantially concurrently electrospraying an ECM-derived (extracellularmatrix-derived) gel onto the substrate. In one embodiment, the substrateis a mandrel, which is rotated during electrospinning. Non-limitingexamples of biodegradable, biocompatible, elastomeric polymercomposition include: PEUU-, PEEUU-, PCUU-, PECUU-, PET- (e.g., DACRON),and TPA-containing compositions.

According to another non-limiting embodiment, one or more layers of awet-electrospun biodegradable, biocompatible, elastomeric polymercomposition are electrospun onto the layer of biodegradable,biocompatible, elastomeric polymer composition mixed with the ECM gel.In one embodiment, the layer of biodegradable, biocompatible,elastomeric polymer composition mixed with the ECM gel is sandwichedbetween two electrospun layers of the wet-electrospun biodegradable,biocompatible, elastomeric polymer composition.

In one embodiment, the biodegradable, biocompatible elastomeric polymercomprises one of PEUU, PEEUU or a mixture thereof. In anotherembodiment, the biodegradable, biocompatible elastomeric polymercomprises polycaprolactone, which has an Mw (weight average molecularweight) of 1000-5000, and in one embodiment, the polycaprolactone has anMw of 2000. As an example, the biodegradable, biocompatible elastomericpolymer comprises, consists essentially of or consists of a copolymer ofpolycaprolactone (Mw˜2000), 1,4-diisocyanobutane and putrescine. In yetanother embodiment, the biodegradable, biocompatible elastomeric polymeris prepared from a polycaprolactone-polyethylene glycolpolycaprolactonetriblock copolymer, an aliphatic diisocyanate and an aliphatic diamine,for example, the aliphatic diisocyanate is 1,4-diisocyanobutane and thealiphatic diamine is putrescine. In certain embodiments, the ECM-derivedgel is prepared from dermal ECM, urinary bladder ECM and/or smallintestine ECM.

In the composition and related methods, the scaffold (scaffoldstructure) comprises >50% wt of the biodegradable, biocompatibleelastomeric polymer, for example and without limitation, the scaffoldcomprises from 70% to 85% wt of the biodegradable, biocompatibleelastomeric polymer, for example approximately 72% wt.

In an alternate embodiment, a multi-layered structure is producedcomprising the above-described ECM gel/polymer electrospun compositionattached to or sandwiched between one or more wet-electrospun layers ofa biodegradable, biocompatible, elastomeric polymer. The methodcomprises concurrently or substantially concurrently electrospinning abiodegradable, biocompatible, elastomeric polymer and spraying a liquid,such as an aqueous liquid, for example and without limitation a liquidselected from the group consisting of water, a physiological saltsolution (e.g., normal saline), a buffer solution (e.g., PBS), amammalian blood product and cell culture medium, onto the substrate,thereby producing a first layer, and concurrently or substantiallyconcurrently electrospinning the biodegradable, biocompatible,elastomeric polymer matrix and electrospraying the ECM-derived(extracellular matrix-derived) gel onto the matrix onto the first layer,thereby producing a second layer. In certain embodiments, the methodcomprises concurrently or substantially concurrently electrospinning abiodegradable, biocompatible, elastomeric polymer and spraying a liquid,such as an aqueous liquid, for example and without limitation a liquidselected from the group consisting of water, a physiological saltsolution (e.g., normal saline), a buffer solution (e.g., PBS), amammalian blood product and cell culture medium, onto the second layer,thereby producing a third layer. As an example, the biodegradable,biocompatible, elastomeric polymer composition comprises one or more of:PEUU-, PEEUU-, PCUU-, PECUU-, PET- (e.g., DACRON), and TPA-containingcompositions, for example, one or both of a poly(ester urethane) urea(PEUU) and a poly(ether ester urethane)urea (PEEUU).

Alternately, the method comprises after electrospinning thebiodegradable, biocompatible, elastomeric polymer composition onto thesubstrate and concurrently or substantially concurrently electrosprayingan ECM-derived (extracellular matrix-derived) gel onto the substrate,concurrently or substantially concurrently electrospinning abiodegradable, biocompatible, elastomeric polymer and spraying a liquid,such as an aqueous liquid, for example and without limitation a liquidselected from the group consisting of water, a physiological saltsolution, a buffer solution, a mammalian blood product and cell culturemedium, onto the substrate.

Also provided is biohybrid scaffold (e.g., scaffold structure, structureor device) comprising a matrix of a biodegradable, biocompatibleelastomeric polymer and an ECM-derived gel interspersed substantiallyevenly throughout the matrix. As indicated above, examples of thebiodegradable, biocompatible elastomeric polymer include one or more of:PEUU-, PEEUU-, PCUU-, PECUU-, PET- (e.g., DACRON), and TPA-containingcompositions. In one non-limiting embodiment, the biodegradable,biocompatible elastomeric polymer comprises a copolymer ofpolycaprolactone (Mw˜2000), 1,4-diisocyanobutane and putrescine. Inadditional embodiments, the biohybrid scaffold further comprises one ormore layers of a wet-electrospun biodegradable, biocompatibleelastomeric polymer attached to the matrix of a biodegradable,biocompatible elastomeric polymer and the ECM-derived gel interspersedsubstantially evenly throughout the matrix, forming a composite scaffoldstructure. In another embodiment, the composite scaffold comprises thematrix of a biodegradable, biocompatible elastomeric polymer and anECM-derived gel interspersed substantially evenly throughout the matrixsandwiched between two layers of the wet-electrospun biodegradable,biocompatible elastomeric polymer. According to one embodiment, thewet-electrospun biodegradable, biocompatible elastomeric polymercomprises a PEUU and PBS, or one or more of an aqueous liquid, forexample and without limitation a liquid selected from the groupconsisting of water, a physiological salt solution, a buffer solution, amammalian blood product and cell culture medium.

Uses for the scaffold structures described herein include a method ofgrowing tissue in a patient comprising implanting a biohybrid scaffoldaccording to any embodiment described herein in a patient at a site ofinjury or defect in the patient. As an example, the biohybrid scaffoldis implanted in an abdominal wall the patient, thereby repairing aninjury or defect in the abdominal wall of the patient.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of a cross section or porcine urinarybladder tissue.

FIG. 2 is a schematic depiction of a three-layer scaffold structure asdescribed herein.

FIG. 3 is a graph depicting mechanical properties of a PEUU preparedeither as a film, a TIPS scaffold or electrospun.

FIG. 4 are photomicrographs showing cross-section morphology of aPEUU/dECM hybrid scaffold (50:50).

FIG. 5 are photomicrographs showing surface morphology of a PEUU/dECMhybrid scaffold (50:50).

FIGS. 6A and 6B are graphs showing mechanical properties of PEUU/dECMhybrid scaffolds at different PEUU/dECM ratios, which were tuned bychanging gel feeding rate (6A—tensile strength, 6B—strain at maximumstress).

FIG. 7 is a graph depicting typical stress-strain curves of a PEUU/dECMgel hybrid scaffold (80/20) at longitudinal and circumferentialdirections.

FIG. 8 provides photographs showing macroscopic images of implants attwo and four weeks post-implant.

FIGS. 9A and 9B show photomicrographs (H&E stains) of two exemplary PEUUsections at two and four weeks, respectively, as described in theExamples below. In FIGS. 9A and 9B, the right and left images are fromdifferent areas of the implant in a single rat.

FIGS. 10A and 10B show photomicrographs (H&E stains) of two exemplaryPEUU/dECM (50-50) sections at two and four weeks, respectively. In FIGS.10A and 10B, the right and left images are from different areas of theimplant in a single rat.

FIGS. 11A and 11B are photomicrographs showing Masson's Trichromestaining of rats' body wall treated with either a PEUU device or adevice of acellular dECM at two and four weeks.

FIGS. 12A and 12B are photomicrographs showing an H&E stain of a ratabdominal wall cross-section repaired using a PEUU/dECM 50/50 hybridscaffold. This shows good tissue infiltration.

FIG. 13 provides graphs showing shows biaxial stress-stretch curves ofnative abdominal wall tissue and PEUU/dECM 50/50 hybrid scaffoldspre-implant and 4 weeks post-implant.

FIGS. 14A and 14B are photomicrographs of H&E stained cross sections ofthe PEUU/dECM 72/28 hybrid implant at two and four weeks, respectively,with left and right panels showing the microscopic results obtained inboth animals implanted.

FIG. 15 shows biaxial stress-stretch curves of native abdominal walltissue and for PEUU/dECM 50/50 hybrid scaffolds pre-implant, 2 and 4weeks post-implant.

FIG. 16 is a graph showing the influence of processing parameters onmechanics of a pre-implantation patch. The numbers in brackets are theprocess conditions of the PEUU solution infusion rate (ml/h) to dermalECM solution infuse rate (ml/min).

FIG. 17 are photomicrographs showing cross sections of the compositestructure prepared by the method of Example 4.

FIG. 18 are photomicrographs of Masson's trichrome stainedcross-sections of the sandwiched sheets, for the three differentelectrospinning durations, as described in Example 4.

FIG. 19 is a photomicrograph of Masson's trichrome stainedcross-sections of the sandwiched sheets (20 minute electrospinningduration), as described in Example 4.

FIGS. 20A and 20B are graphs showing stress (FIG. 20A) and strain (FIG.20B) values for the three composite structures prepared according to themethods described in Example 4, as compared to PEUU/dECM (72/28).

FIG. 21 are graphs providing comparisons of biaxial mechanical testingfor the sandwich composite, PEUU/dECM material, native abdominal wallmuscle tissue and a Dacron/dECM gel biohybrid, as described in Example4.

FIG. 22 are photomicrographs showing H&E and Masson's trichrome stainsof that explanted tissue, as described in Example 4. Low magnificationimages (upper row, scale bar=1 mm) and high magnification images (bottomrow, scale bar=100 μm).

FIG. 23 are graphs providing comparisons of biaxial mechanical testingfor the explanted sandwich composite, explanted PEUU/dECM (72:28)material, and native abdominal wall muscle tissue, as described inExample 4, at four and eight weeks post-implant.

FIG. 24 is a graph showing suture retention strength of sandwichscaffold tuning by wet-electrospinning time, indicating the superiorityof the sandwiched material as compared to the PEUU/dECM (72:28)material, as described in Example 4.

DETAILED DESCRIPTION

The use of numerical values in the various ranges specified in thisapplication, unless expressly indicated otherwise, are stated asapproximations as though the minimum and maximum values within thestated ranges are both preceded by the word “about”. In this manner,slight variations above and below the stated ranges can be used toachieve substantially the same results as values within the ranges.Also, unless indicated otherwise, the disclosure of these ranges isintended as a continuous range including every value between the minimumand maximum values.

As used herein, the “treatment” or “treating” of a wound or defect meansadministration to a patient by any suitable dosage regimen, procedureand/or administration route of a composition, device or structure withthe object of achieving a desirable clinical/medical end-point,including attracting progenitor cells, healing a wound, correcting adefect, etc.

As used herein, the terms “comprising,” “comprise” or “comprised,” andvariations thereof, are meant to be open ended. The terms “a” and “an”are intended to refer to one or more.

As used herein, the term “patient” or “subject” refers to members of theanimal kingdom including but not limited to human beings and “mammal”refers to all mammals, including, but not limited to human beings.

A biodegradable polymer composition is “biocompatible” in that thepolymer and degradation products thereof are substantially non-toxic tocells or organisms within acceptable tolerances, including substantiallynon-carcinogenic and substantially non-immunogenic, and are cleared orotherwise degraded in a biological system, such as an organism (patient)without substantial toxic effect. Non-limiting examples of degradationmechanisms within a biological system include chemical reactions,hydrolysis reactions, and enzymatic cleavage.

As used herein, the term “polymer composition” is a compositioncomprising one or more polymers. As a class, “polymers” includes,without limitation, homopolymers, heteropolymers, co-polymers, blockpolymers, block co-polymers and can be both natural and synthetic.Homopolymers contain one type of building block, or monomer, whereascopolymers contain more than one type of monomer. The term “(co)polymer”and like terms refer to either homopolymers or copolymers.

A polymer “comprises” or is “derived from” a stated monomer if thatmonomer is incorporated into the polymer. Thus, the incorporated monomerthat the polymer comprises is not the same as the monomer prior toincorporation into a polymer, in that at the very least, certain groupsare missing and/or modified when incorporated into the polymer backbone.A polymer is said to comprise a specific type of linkage if that linkageis present in the polymer.

As described herein, a “fiber” an elongated, slender, thread-like and/orfilamentous structure. A “matrix” is any two- or three-dimensionalarrangement of elements (e.g., fibers), either ordered (e.g., in a wovenor non-woven mesh) or randomly-arranged (as is typical with a mat offibers typically produced by electrospinning) and can be isotropic oranisotropic.

By “biodegradable or “bioerodable”, it is meant that a polymer, onceimplanted and placed in contact with bodily fluids and tissues, willdegrade either partially or completely through chemical reactions withthe bodily fluids and/or tissues, typically and often preferably over atime period of hours, days, weeks or months. Non-limiting examples ofsuch chemical reactions include acid/base reactions, hydrolysisreactions, and enzymatic cleavage. The biodegradation rate of thepolymer matrix may be manipulated, optimized or otherwise adjusted sothat the matrix degrades over a useful time period. The polymer orpolymers typically will be selected so that it degrades in situ over atime period to optimize mechanical conditioning of the tissue. Forinstance, in the case of abdominal wall repair, it is desirable that thematrix dissolves over at least a week and preferably longer. Moreimportantly, the matrix would have to retain its supportive capacityuntil tissue remodeling occurs, such as for at least 2-8 weeks, orlonger.

According to a first embodiment, the structures described hereincomprise a biodegradable, elastomeric polymer component and an ECM gelcomponent. As used herein, compositions of matter comprising thedescribed polymeric components and ECM gel, optionally in combinationwith additional layers, such as wet-electrospun layers, are genericallyreferred to herein as “scaffolds” and “structures,” which includes as aclass, without limitation, scaffolds, matrices, biological scaffolds ormatrices, cell growth scaffolds or matrices, etc. The typicalbiodegradable, elastomeric polymer component, when implanted, showslimited cellular infiltration. The ECM gel component, while useful inpromoting cell growth (including, but not limited to one or more ofcolonization, propagation, infiltration, cell viability,differentiation, tissue repair), has insubstantial strength for use as atissue repair scaffold in a patient that requires physical strength. Ithas been found that a simple 50-50 (50% biodegradable, elastomericpolymer:50% ECM gel (1:1), by dry weight of the polymer) mixture ofbiodegradable, elastomeric polymer to ECM gel is not optimal. Applicantshave determined that the ratio of biodegradable, elastomeric polymer toECM gel that shows excellent cellular infiltration, while displayingadequate tensile strength and elasticity, is >50%:<50% and preferablyfrom 70%-85%:15%-30%. This can be achieved by codepositing thebiodegradable, elastomeric polymer and the ECM gel by e.g.,electrospinning. As described herein, the biodegradable, elastomericpolymer is electrospun and the ECM gel is sprayed, e.g. electrosprayed.

The ECM gels described herein are derived from ECM-derived scaffoldmaterial. An “ECM-derived material,” is a material prepared from anextracellular matrix-containing tissue. Any type of extracellular matrixscaffold material can be used to produce the gels in the methods,compositions and devices as described herein (see generally, U.S. Pat.Nos. 4,902,508; 4,956,178; 5,281,422; 5,352,463; 5,372,821; 5,554,389;5,573,784; 5,645,860; 5,771,969; 5,753,267; 5,762,966; 5,866,414;6,099,567; 6,485,723; 6,576,265; 6,579,538; 6,696,270; 6,783,776;6,793,939; 6,849,273; 6,852,339; 6,861,074; 6,887,495; 6,890,562;6,890,563; 6,890,564; and 6,893,666). In certain embodiments, the ECM isisolated from a vertebrate animal, for example and without limitation,from a mammal, including, but not limited to, human, monkey, pig, cowand sheep. The ECM can be derived from any organ or tissue, includingwithout limitation, urinary bladder, intestine, liver, esophagus anddermis. In one embodiment, the ECM is isolated from a urinary bladder.The ECM may or may not include the basement membrane portion of the ECM.In certain embodiments, the ECM includes at least a portion of thebasement membrane.

In one embodiment, the ECM is isolated from harvested porcine urinarybladder to prepare urinary bladder matrix (UBM). Excess connectivetissue and residual urine are removed from the urinary bladder. Thetunica serosa, tunica muscularis externa, tunica submucosa and most ofthe muscularis mucosa (layers G, F, E and mostly D in FIG. 1) can beremoved mechanical abrasion or by a combination of enzymatic treatment,hydration, and abrasion. Mechanical removal of these tissues can beaccomplished by abrasion using a longitudinal wiping motion to removethe outer layers (particularly the abluminal smooth muscle layers) andeven the luminal portions of the tunica mucosa (epithelial layers).Mechanical removal of these tissues is accomplished by removal ofmesenteric tissues with, for example, Adson-Brown forceps and Metzenbaumscissors and wiping away the tunica muscularis and tunica submucosausing a longitudinal wiping motion with a scalpel handle or other rigidobject wrapped in moistened gauze. The epithelial cells of the tunicamucosa (layer A of FIG. 1) can also be dissociated by soaking the tissuein a de-epithelializing solution, for example and without limitation,hypertonic saline. The resulting UBM comprises basement membrane of thetunica mucosa and the adjacent tunica propria (layers B and C of FIG.1), which is further treated with peracetic acid, lyophilized andpowdered. Additional examples are provided below and are also present inthe related art.

In another embodiment, the epithelial cells can be delaminated first byfirst soaking the tissue in a de-epithelializing solution such ashypertonic saline, for example and without limitation, 1.0 N saline, forperiods of time ranging from 10 minutes to 4 hours. Exposure tohypertonic saline solution effectively removes the epithelial cells fromthe underlying basement membrane. The tissue remaining after the initialdelamination procedure includes epithelial basement membrane and thetissue layers abluminal to the epithelial basement membrane. This tissueis next subjected to further treatment to remove the majority ofabluminal tissues but not the epithelial basement membrane. The outerserosal, adventitial, smooth muscle tissues, tunica submucosa and mostof the muscularis mucosa are removed from the remainingde-epithelialized tissue by mechanical abrasion or by a combination ofenzymatic treatment, hydration, and abrasion.

In one embodiment, the ECM is prepared by abrading porcine bladdertissue to remove the outer layers including both the tunica serosa andthe tunica muscularis (layers G and F in FIG. 1) using a longitudinalwiping motion with a scalpel handle and moistened gauze. Followingeversion of the tissue segment, the luminal portion of the tunica mucosa(layer H in FIG. 1) is delaminated from the underlying tissue using thesame wiping motion. Care is taken to prevent perforation of thesubmucosa (layer E of FIG. 1). After these tissues are removed, theresulting ECM consists mainly of the tunica submucosa (layer E of FIG.1).

ECM-derived material can be decelluarized, sterilized and/or dried byany useful method. ECM-derived material can then be used in any form inthe methods and compositions described herein. For instance, thecompounds described herein can be applied to sheets of ECM or comminutedECM to prepare a scaffold suitable to apply to any location in apatient, such as a skin, cartilage, muscle, bone, or nerve growthscaffold.

The ECM can be sterilized by any of a number of standard methods withoutloss of its ability to induce endogenous tissue growth. For example, thematerial can be sterilized by propylene oxide or ethylene oxidetreatment, gamma irradiation treatment (0.05 to 4 mRad), gas plasmasterilization, peracetic acid sterilization, or electron beam treatment.The material can also be sterilized by treatment with glutaraldehyde,which causes cross linking of the protein material, but this treatmentsubstantially alters the material such that it is slowly resorbed or notresorbed at all and incites a different type of host remodeling whichmore closely resembles scar tissue formation or encapsulation ratherthan constructive remodeling. Cross-linking of the protein material canalso be induced with carbodiimide or dehydrothermal or photooxidationmethods. More typically, ECM is disinfected by immersion in 0.1% (v/v)peracetic acid (σ), 4% (v/v) ethanol, and 96% (v/v) sterile water for 2h. The ECM material is then washed twice for 15 min with PBS (pH=7.4)and twice for 15 min with deionized water.

Commercially available ECM preparations can also be used in the methods,devices and compositions described herein. In one embodiment, the ECM isderived from small intestinal submucosa or SIS. Commercially availablepreparations include, but are not limited to, Surgisis™, Surgisis-ES™,Stratasis™, and Stratasis-ES™ (Cook Urological Inc.; Indianapolis, Ind.)and GraftPatch™ (Organogenesis Inc.; Canton Mass.). In anotherembodiment, the ECM is derived from dermis. Commercially availablepreparations include, but are not limited to Pelvicol™ (crosslinkedporcine dermal collagen, sold as Permacol™ in Europe; Bard MedicalDivision, Covington, Ga.), Repliform™ (Microvasive; Boston, Mass.) andAlloderm™ (LifeCell; Branchburg, N.J.). In another embodiment, the ECMis derived from urinary bladder. Commercially available preparationsinclude, but are not limited to UBM (Acell Corporation; Jessup, Md.).

An extracellular matrix-derived gel is described herein. In its broadestsense, ECM-derived scaffold materials are communited and solubilized toform a hydrogel. The solubilized hydrogel may or may not be dialyzed.Solubilization may be achieved by digestion with a suitable protease,such as the endoproteases trypsin, chymotrypsin, pepsin, papain andelastase. In certain non-limiting embodiments, the method for makingsuch a gel comprises: (i) comminuting an extracellular matrix, (ii)solubilizing intact, non-dialyzed or non-cross-linked extracellularmatrix by digestion with an acid protease in an acidic solution toproduce a digest solution, (iii) raising the pH of the digest solutionto a pH between 7.2 and 7.8 to produce a neutralized digest solution,and (iv) gelling the solution at a temperature greater thanapproximately 25° C.

As described above, the ECM typically is derived from mammalian tissue,such as, without limitation from one of urinary bladder, dermis, spleen,liver, heart, pancreas, ovary, or small intestine. In one embodiment,the ECM-derived scaffold material is crosslinked porcine dermalcollagen, e.g., Pelvicol™ (Bard Medical Division, Covington, Ga.) Incertain embodiments, the ECM is derived from a pig, cow, horse, monkey,or human. In one non-limiting embodiment, the ECM is lyophilized andcomminuted. The ECM is then solubilized with an acid protease. The acidprotease may be, without limitation, pepsin or trypsin, and in oneembodiment is pepsin. The ECM typically is solubilized at an acid pHsuitable or optimal for the protease, such as greater than about pH 2,or between pH 2 and 4, for example in a 0.01M HCl solution. The solutiontypically is solubilized for 12-48 hours, depending upon the tissue type(e.g., see examples below), with mixing (stirring, agitation, admixing,blending, rotating, tilting, etc.). Once the ECM is solubilized the pHis raised to between 7.2 and 7.8, and according to one embodiment, to pH7.4. Bases, such as bases containing hydroxyl ions, including NaOH, canbe used to raise the pH of the solution. Likewise buffers, such as anisotonic buffer, including, without limitation, Phosphate BufferedSaline (PBS), can be used to bring the solution to a target pH, or toaid in maintaining the pH and ionic strength of the gel to targetlevels, such as physiological pH and ionic conditions. The neutralizeddigest solution can be gelled at temperatures approaching 37° C.,typically at any temperature over 25° C., though gelation proceeds muchmore rapidly at temperatures over 30° C., and as the temperatureapproaches physiological temperature. The method typically does notinclude a dialysis step prior to gelation, yielding a more-completeECM-like matrix that typically gels at 37° C. more slowly thancomparable collagen or dialyzed ECM preparations.

The ECM gel can be sprayed as a liquid or hydrogel in the methodsprovided herein. An ECM gel may have an LCST (Lower Critical SolutionTemperature) above or below the temperature at which the solution issprayed, and as such will have a gel transition at a temperature higher,equal to or lower than the temperature at which the ECM gel is sprayed.For example, if the hydrogel is sprayed at room temperature (that isapproximately 20-25° C.) or less and the LCST of the ECM material isgreater than the spraying temperature, but, e.g., less than 37° C., thematerial can be sprayed and will later gel on warming, for example onimplantation. Thus, an ECM gel with an LCST between 20° C. and 37° C.,for example and without limitation approximately 25° C., is useful inthe compositions and methods described herein. See, e.g. United StatesPatent Publication No. 20080260831, incorporated herein by reference forits technical disclosure. See also, Stankus et al., Hybrid nanofibrousscaffolds from electrospinning of a synthetic biodegradable elastomerand urinary bladder matrix, J Biomater. Sci. Polym. Ed. (2008)19(5):635-652. In that reference, PEUU was mixed with solubilized UBMECM and was electrospun. Although UBM prepared in this manner may finduse co-electrospun with PEUU rather than electrospun in the samemixture, cells do not permeate the matrix of that reference as well asdesired or as well as the scaffolds described herein. The ECM gel, whenelectrosprayed, is not necessarily a gel at that time, but is indicatedas being a gel due to its final, intended physical form in the scaffoldstructures described herein, and thus the phrase “ECM gel” includespre-gels—compositions that are in the process of gelling whenelectrosprayed, or which are gelled in the scaffold product, e.g., byheating to 37° C.

As used herein, the term “polymer” refers to both synthetic polymericcomponents and biological polymeric components. “Biological polymer(s)”are polymers that can be obtained from biological sources, such as,without limitation, mammalian or vertebrate tissue, as in the case ofcertain extracellular matrix-derived (ECM-derived) compositions,described above. Biological polymers can be modified by additionalprocessing steps. Polymer(s), in general include, for example andwithout limitation, mono-polymer(s), copolymer(s), polymeric blend(s),block polymer(s), block copolymer(s), cross-linked polymer(s),non-cross-linked polymer(s), linear-, branched-, comb-, star-, and/ordendrite-shaped polymer(s), where polymer(s) can be formed into anyuseful form, for example and without limitation, a hydrogel, a porousmesh, a fiber, woven mesh, or non-woven mesh, such as, for example andwithout limitation, as a non-woven mesh formed by electrospinning.

Generally, the polymeric components suitable for the structuresdescribed herein are any polymer that is biocompatible and can bebiodegradable. In certain non-limiting embodiments, the biodegradablepolymers may comprise homopolymers, copolymers, and/or polymeric blendscomprising, without limitation, one or more of the following monomers:glycolide, lactide, caprolactone, dioxanone, and trimethylene carbonate.In other non-limiting embodiments, the polymer(s) comprise labilechemical moieties, non-limiting examples of which include esters,anhydrides, polyanhydrides, or amides, which can be useful in, forexample and without limitation, controlling the degradation rate of thescaffold and/or the release rate of therapeutic agents from thescaffold. Alternatively, the polymer(s) may contain polypeptides orbiomacromolecules as building blocks which are susceptible to chemicalreactions once placed in situ. In one non-limiting example, the polymercomposition comprises a polypeptide comprising the amino acid sequencealanine-alanine-lysine, which confers enzymatic lability to the polymer.In another non-limiting embodiment, the polymer composition may comprisea biomacromolecular component derived from an ECM. For example, asdescribed in further detail below, the polymer composition may comprisethe biomacromolecule collagen so that collagenase, which is present insitu, can degrade the collagen. The polymers used herein may beelastomeric, meaning they change shape on application of a deformingforce and substantially return to an original shape when the deformingforce is removed.

In another non-limiting embodiment, the synthetic polymeric componentcomprises any hydrolytically, chemically, biochemically, and/orproteolytically labile group, non-limiting examples of which include anester moiety, amide moiety, anhydride moiety, specific peptidesequences, and generic peptide sequences.

A number of biocompatible, biodegradable elastomeric (co)polymers areknown and have been established as useful in preparing cell growthmatrices, including biodegradable poly(ester urethane) urea (PEUU),poly(ether ester urethane)urea (PEEUU), poly(ester carbonate)urethaneurea (PECUU) and poly(carbonate)urethane urea (PCUU). In general, useful(co)polymers comprise monomers derived from alpha-hydroxy acidsincluding polylactide, poly(lactide-co-glycolide),poly(L-lactide-co-caprolactone), polyglycolic acid,poly(dl-lactide-co-glycolide), poly(l-lactide-co-dl-lactide); monomersderived from esters including polyhydroxybutyrate, polyhydroxyvalerate,polydioxanone and polygalactin; monomers derived from lactones includingpolycaprolactone; monomers derived from carbonates includingpolycarbonate, polyglyconate, poly(glycolide-co-trimethylene carbonate),poly(glycolide-co-trimethylene carbonate-co-dioxanone); monomers joinedthrough urethane linkages, including polyurethane, poly(ester urethane)urea elastomer.

In certain embodiments, the polymers used to make the structuresdescribed herein also release therapeutic agents when they degradewithin the patient's body. For example, the individual building blocksof the polymers may be chosen such that the building blocks themselvesprovide a therapeutic benefit when released in situ through thedegradation process. In one embodiment, one of the polymer buildingblocks is putrescine, which has been implicated as a substance thatcauses cell growth and cell differentiation.

The biodegradable polymers may be, without limitation, homopolymers,copolymers, and/or polymeric blends. According to certain embodiments,the polymer(s) comprise, without limitation, one or more of thefollowing monomers: glycolide, lactide, caprolactone, dioxanone, andtrimethylene carbonate. According to certain embodiments, the polymer ischosen from one or more of: a polymer derived from an alpha-hydroxyacid, a polylactide, a poly(lactide-co-glycolide), apoly(L-lactide-co-caprolactone), a polyglycolic acid, apoly(dl-lactide-co-glycolide), a poly(l-lactide-co-dl-lactide), apolymer comprising a lactone monomer, a polycaprolactone, polymercomprising carbonate linkages, a polycarbonate, a polyglyconate, apoly(trimethylene carbonate), a poly(glycolide-co-trimethylenecarbonate), a poly(glycolide-co-trimethylene carbonate-co-dioxanone), apolymer comprising urethane linkages, a polyurethane, a poly(esterurethane) urea, a poly(ester urethane) urea elastomer, a poly(estercarbonate urethane) urea, a poly(carbonate urethane) urea, apolycarbonate urethane, a polyester urethane, a polymer comprising esterlinkages, a polyalkanoate, a polyhydroxybutyrate, a polyhydroxyvalerate,a polydioxanone, a polygalactin, a natural polymer, chitosan, collagen,elastin, alginate, cellulose, hyaluronic acid and gelatin. In oneembodiment, the polymer composition comprises a poly(ester urethane)urea with from about 25% wt. to about 75% wt. collagen. The polymercomposition also may comprise elastin, collagen or a mixture thereof,for example and without limitation from about 25% wt. to about 75% wt.of a mixture of collagen and elastin, which are, according to oneembodiment, in approximately (about) equal amounts. In one non-limitingembodiment, the polymer comprises a polycaprolactone. In anotherembodiment, the polymer comprises a polycaprolactone diol. In yetanother embodiment, the polymer comprises a triblock copolymercomprising polycaprolactone, poly(ethylene glycol), and polycaprolactoneblocks

In another non-limiting embodiment, the polymer composition may comprisea biomacromolecular component derived from an ECM. For example, thepolymer composition may comprise the biomacromolecule collagen so thatcollagenase, which is present in situ, can degrade the collagen.According to a non-limiting embodiment, the polymer compositioncomprises one or both of a collagen and an elastin. Collagen is a commonECM component and typically is degraded in vivo at a rate faster thanmany synthetic bioerodable polymers. Therefore, manipulation of collagencontent in the polymer composition can be used as a method of modifyingbioerosion rates in vivo. Collagen may be present in the polymercomposition in any useful range, including, without limitation, fromabout 2% wt. to about 95% wt., but more typically in the range of fromabout 25% wt. to about 75% wt., inclusive of all ranges and pointstherebetween, including from about 40% wt. to about 75% wt., includingabout 75% wt. and about 42.3% wt. Elastin may be incorporated into thepolymer composition in order to provide increased elasticity. Use ofelastin can permit slight circumferential expansion of the restrictivematrix in order to assist the tubular tissue, such as a vein, adapt toits new function, such as an arterial use. Elastin may be present in thepolymer composition in any useful range, including without limitation,from about 2% wt. to about 50% wt., inclusive of all ranges and pointstherebetween, including from about 40% wt. and about 42.3% wt.,inclusive of all integers and all points therebetween and equivalentsthereof. In one non-limiting embodiment, collagen and elastin arepresent in approximately equal amounts in the polymer composition, Inanother embodiment, the sum of the collagen and elastin content in thepolymer composition is in any useful range, including, withoutlimitation, from about 2% wt. to about 95% wt., but more typically inthe range of from about 25% wt. to about 75% wt., inclusive of allranges and points therebetween, including from about 40% wt. to about75% wt., including about 75% wt. and about 42.3% wt.

In one non-limiting embodiment, the polymer composition comprises abiodegradable poly(ester urethane) urea elastomer (PEUU). PEUU can bemanufactured by reacting a diol with a diisocyanate to form a prepolymerand then reacting the prepolymer with a diamine. A non-limiting exampleof such a PEUU is an elastomeric polymer made from polycaprolactone diol(Mw 2000) and 1,4-diisocyanatobutane, using a diamine chain extendersuch as putrescine. One non-limiting example or a method for preparing aPEUU polymer is a two-step polymerization process wherebypolycaprolactone diol (Mw 2000), 1,4-diisocyanatobutane, and diamine arecombined in a 2:1:1 molar ratio. In the first step to form theprepolymer, a 15 wt % solution of 1,4-diisocyanatobutane in DMSO(dimethyl sulfoxide) is stirred continuously with a 25 wt % solution ofpolycaprolactone diol in DMSO. Then, stannous octoate is added and themixture is allowed to react at 75° C. for 3 hours. In the second step,the prepolymer is reacted with a diamine to extend the chain and to formthe polymer. In one embodiment, the diamine is putrescine, which isadded drop-wise while stirring and allowed to react at room temperaturefor 18 hours. In one embodiment, the diamine is lysine ethyl ester,which is dissolved in DMSO with triethylamine, added to the prepolymersolution, and allowed to react at 75° C. for 18 hours. After the twostep polymerization process, the polymer solution is precipitated indistilled water. Then, the wet polymer is immersed in isopropanol forthree days to remove any unreacted monomers. Finally, the polymer isdried under vacuum at 50° C. for 24 hours.

In another non-limiting embodiment, the polymer composition comprisespoly(ether ester urethane) urea elastomer (PEEUU). For example andwithout limitation, the PEEUU may be made by reactingpolycaprolactone-b-polyethylene glycol-b-polycaprolactone triblockcopolymers with 1,4-diisocyanatobutane and putrescine. In onenon-limiting embodiment, PEEUU is obtained by a two-step reaction usinga 2:1:1 reactant stoichiometry of 1,4-diisocyanatobutane:triblockcopolymer:putrescine. According to one non-limiting embodiment, thetriblock polymer can be prepared by reacting poly(ethylene glycol) andε-caprolactone with stannous octoate at 120° C. for 24 hours under anitrogen environment. The triblock copolymer is then washed with ethylether and hexane, then dried in a vacuum oven at 50° C. In the firststep to form the prepolymer, a 15 wt % solution of1,4-diisocyanatobutane in DMSO is stirred continuously with a 25 wt %solution of triblock copolymer in DMSO. Then, stannous octoate is addedand the mixture is allowed to react at 75° C. for 3 hours. In the secondstep, putrescine is added drop-wise under stirring to the prepolymersolution and allowed to react at room temperature for 18 hours. ThePEEUU polymer solution is then precipitated with distilled water. Thewet polymer is immersed in isopropanol for 3 days to remove unreactedmonomer and dried under vacuum at 50° C. for 24 hours.

In another non-limiting embodiment, the polymer composition comprises apoly(ester carbonate)urethane urea (PECUU) or a poly(carbonate)urethaneurea (PCUU), which are described, for example, in Hong et al. (Tailoringthe degradation kinetics of poly(ester carbonate urethane)ureathermoplastic elastomers for tissue engineering scaffolds Biomaterials,Biomaterials 31 (2010) 4249-4258). Poly(ester carbonate urethane)urea(PECUU) is synthesized, for example using a blended soft segment ofpolycaprolactone (PCL) and poly(1,6-hexamethylene carbonate) (PHC) and ahard segment of 1,4-diisocyanatobutane (BDI) with chain extension byputrescine. Different molar ratios of PCL and PHC can be used to achievedifferent physical characteristics. Putrescine is used as a chainextender by a two-step solvent synthesis method. In one example, the(PCL+PHC):BDI:putrescine molar ratio is defined as 1:2:1. Variable molarratios of PCL and PHC (e.g., PCL/PHC ratios of 100/0 (yielding a PEUU),75/25, 50/50, 25/75 and 0/100 (yielding a PCUU)) are completelydissolved in DMSO in a 3-neck flask with argon protection and then BDIis added to the solution, following 4 drops of Sn(Oct)₂. The flask isplaced in an oil bath at 70° C. After 3 h, the prepolymer solution iscooled at room temperature and then a putrescine/DMSO solution is addeddropwise into the agitated solution. The final polymer solutionconcentration is controlled to be approximately 4% (w/v). Then the flaskis than placed in an oil bath and kept at 70° C. overnight. The polymeris precipitated in an excess volume of cool deionized water and thendried in a vacuum at 60° C. for 3 days. The polyurethane ureassynthesized from the different PCL/PHC molar ratios defined above arereferred to as PEUU, PECUU 75/25, PECUU 50/50, PECUU 25/75 and PCUU,respectively. In practice, the yields of all final products using thismethod is approximately 95%.

As indicated above, diamines and diols are useful building blocks forpreparing the (co)polymer compositions described herein. Diamines asdescribed above have the structure H₂N—R—NH₂ where “R” is an aliphaticor aromatic hydrocarbon or a hydrocarbon comprising aromatic andaliphatic regions. The hydrocarbon may be linear or branched. Examplesof useful diamines are putrescine (R=butylene) and cadaverine(R=pentylene). Useful diols include polycaprolactone (e.g., Mw1000-5000), multi-block copolymers, such as polycaprolactone-PEGcopolymers, including polycaprolactone-b-polyethyleneglycol-b-polycaprolactone triblock copolymers of varying sizes. Otherbuilding blocks for useful diols include, without limitation glycolides(e.g. polyglycolic acid (PGA)), lactides, dioxanones, and trimethylenecarbonates. Diisocyanates have the general structure OCN—R—NCO, where“R” is an aliphatic or aromatic hydrocarbon or a hydrocarbon comprisingaromatic and aliphatic regions. The hydrocarbon may be linear orbranched.

In additional embodiments, the polymer composition comprisespolyethylene terephthalate (PET, e.g., DACRON). Of note, PET is lessbiodegradable than the copolymers described above, and is stiffer. PETscaffolds structures are made essentially in the manned described hereinfor PEUU and other polymer compositions described herein. Polymerconcentrations and infusion rates may be altered to accommodate thedifferent qualities of the PET composition, for example and withoutlimitation, for PET, 20% w/v in HFIP at 12 mL/h infusion rate, as usedin the examples below.

In other embodiments, the polymer composition comprises a tyrosinepolyarylate (TPA). As with PET, TPA is less biodegradable than thepolyurethane copolymers described above, and also is stiffer. TPAscaffolds structures are made essentially in the manned described hereinfor PEUU and other polymer compositions. Polymer concentrations andinfusion rates may be altered to accommodate the different qualities ofthe TPA composition, for example and without limitation, for TPA, 12%w/v in HFIP at 20 mL/h infusion rate, as used in the examples below.Tyrosine polyarylates are commonly prepared from an aliphatic acid and atyrosine-derived diphenol. Non-limiting examples of useful aliphaticacids include: succinic acid, adipic acid, sebacic acid, anddicarboxylic acid chlorides or anhydrides. Non-limiting examples oftyrosine-derived diphenols include desaminotyrosyl-tyrosine alkylesters, where the alkyl is, for example, one of ethyl, hexyl and octyl)(DTE). As an example, in the Examples below, Poly(DTE-co-27.5 DTsuccinate) was used. TPAs and methods of making TPAs are described, forexample, in U.S. Pat. No. 5,216,115 and United States Patent PublicationNo. 2011/0082545, each of which is incorporated herein by reference forits technical disclosure, disclose useful TPAs. Additional referencesdisclosing TPA compositions and methods of making and using thosecompositions include: Fiordeliso, J, et al. (1994) Design, synthesis,and preliminary characterization of tyrosine-containing polyarylates:new biomaterials for medical applications, J Biomater Sci Polym Ed.1994; 5(6):497-510; Huang, X et al. (2009) A library ofL-tyrosine-derived biodegradable polyarylates for potential biomaterialapplications, part I: synthesis, characterization and acceleratedhydrolytic degradation J Biomater Sci Polym Ed. 2009; 20(7-8):935-55;and Bourke, S L et al. (2003) Polymers derived from the amino acidL-tyrosine: polycarbonates, polyarylates and copolymers withpoly(ethylene glycol) Adv Drug Deliv Rev. 2003 Apr. 25; 55(4):447-66.

In another embodiment, at least one therapeutic agent is added to thescaffold or composition described herein before it is implanted in thepatient or otherwise administered to the patient. Generally, thetherapeutic agents include any substance that can be coated on, embeddedinto, absorbed into, adsorbed to, or otherwise attached to orincorporated onto or into the structure or incorporated into a drugproduct that would provide a therapeutic benefit to a patient.Non-limiting examples of such therapeutic agents include antimicrobialagents, growth factors, emollients, retinoids, and topical steroids.Each therapeutic agent may be used alone or in combination with othertherapeutic agents. For example and without limitation, a structurecomprising neurotrophic agents or cells that express neurotrophic agentsmay be applied to a wound that is near a critical region of the centralnervous system, such as the spine. Alternatively, the therapeutic agentmay be blended with the polymer while a polymer is being processed. Forexample, the therapeutic agent may be dissolved in a solvent (e.g.,DMSO) and added to the polymer blend during processing. In anotherembodiment, the therapeutic agent is mixed with a carrier polymer (e.g.,polylactic-glycolic acid microparticles) which is subsequently processedwith an elastomeric polymer. By blending the therapeutic agent with acarrier polymer or elastomeric polymer itself, the rate of release ofthe therapeutic agent may be controlled by the rate of polymerdegradation.

In certain non-limiting embodiments, the therapeutic agent is a growthfactor, such as a neurotrophic or angiogenic factor, which optionallymay be prepared using recombinant techniques. Non-limiting examples ofgrowth factors include basic fibroblast growth factor (bFGF), acidicfibroblast growth factor (aFGF), vascular endothelial growth factor(VEGF), hepatocyte growth factor (HGF), insulin-like growth factors 1and 2 (IGF-1 and IGF-2), platelet derived growth factor (PDGF), stromalderived factor 1 alpha (SDF-1 alpha), nerve growth factor (NGF), ciliaryneurotrophic factor (CNTF), neurotrophin-3, neurotrophin-4,neurotrophin-5, pleiotrophin protein (neurite growth-promoting factor1), midkine protein (neurite growth-promoting factor 2), brain-derivedneurotrophic factor (BDNF), tumor angiogenesis factor (TAF),corticotrophin releasing factor (CRF), transforming growth factors α andτ (TGF-α and TGF-β), interleukin-8 (IL-8), granulocyte-macrophage colonystimulating factor (GM-CSF), interleukins, and interferons. Commercialpreparations of various growth factors, including neurotrophic andangiogenic factors, are available from R & D Systems, Minneapolis,Minn.; Biovision, Inc, Mountain View, Calif.; ProSpec-Tany TechnoGeneLtd., Rehovot, Israel; and Cell Sciences®, Canton, Mass.

In certain non-limiting embodiments, the therapeutic agent is anantimicrobial agent, such as, without limitation, isoniazid, ethambutol,pyrazinamide, streptomycin, clofazimine, rifabutin, fluoroquinolones,ofloxacin, sparfloxacin, rifampin, azithromycin, clarithromycin,dapsone, tetracycline, erythromycin, ciprofloxacin, doxycycline,ampicillin, amphotericin B, ketoconazole, fluconazole, pyrimethamine,sulfadiazine, clindamycin, lincomycin, pentamidine, atovaquone,paromomycin, diclazaril, acyclovir, trifluorouridine, foscarnet,penicillin, gentamicin, ganciclovir, iatroconazole, miconazole,Zn-pyrithione, and silver salts such as chloride, bromide, iodide andperiodate.

In certain non-limiting embodiments, the therapeutic agent is ananti-inflammatory agent, such as, without limitation, an NSAID, such assalicylic acid, indomethacin, sodium indomethacin trihydrate,salicylamide, naproxen, colchicine, fenoprofen, sulindac, diflunisal,diclofenac, indoprofen, sodium salicylamide; an anti-inflammatorycytokine; an anti-inflammatory protein; a steroidal anti-inflammatoryagent; or an anti-clotting agents, such as heparin. Other drugs that maypromote wound healing and/or tissue regeneration may also be included.

Structures described herein are preferably made by electrospinning ofthe biodegradable, elastomeric polymer, and concurrent deposition of theECM gel, and/or where appropriate a blood product or other liquid, byspraying, e.g., electrospraying. Other compounds or components may beincorporated into a structure as described herein by any method,including absorption, adsorption, mixing, etc.

The deposited biodegradable, elastomeric polymer typically is porous. Asused herein, the term “porosity” refers to a ratio between a volume ofall the pores within the polymer composition and a volume of the wholepolymer composition. For instance, a polymer composition with a porosityof 85% would have 85% of its volume containing pores and 15% of itsvolume containing the polymer. In certain non-limiting embodiments, theporosity of the structure is at least 60%, 65%, 70%, 75%, 80%, 85%, or90%, or increments therebetween. In another non-limiting embodiment, theaverage pore size of the structure is between 0.1 and 300 microns, 0.1and 100 microns, 1-25 microns, including increments therebetween. Forexample and without limitation, a structure that acts as a barrier tobacteria and other pathogens may have an average pore size of less than0.5 microns or less than 0.2 microns. The structures described hereinare manufactured by electrospinning. It therefore is often advantageousto adjust the pore size or degree of porosity by varying the polymerconcentration of the electrospinning solution or by varying the spinningdistance from the nozzle to the target. For example and withoutlimitation, the average pore size may be increased by increasing theamount of polymeric components within the suspension used forelectrospinning, which results in larger fiber diameters and thereforelarger pore sizes. In another non-limiting example, the average poresize can be increased by increasing spinning distance from the nozzle tothe target, which results in less adherence between fibers and a loosermatrix. Where ECM gel is co-deposited during the electrospinning, manyof the pores (that is a large percentage of the pores or interstices) inthe deposited polymer are filled with the ECM gel.

In certain preferred embodiments, electrospinning is used to deposit thebiodegradable, elastomeric polymer and optionally the ECM gel and/orother liquid, such as a mammalian blood product, media buffer solution,medium, etc. In its simplest sense, electrospinning is caused by thedeposit of a liquid composition, such as polymer fibers onto a targetsurface caused by an electric potential. Electrospinning methods arewell-known in the field of tissue engineering and are conductedessentially as described below. Electrospinning permits fabrication ofstructures that resemble the scale and fibrous nature of the nativeextracellular matrix (ECM). The ECM is composed of fibers, pores, andother surface features at the sub-micron and nanometer size scale. Suchfeatures directly impact cellular interactions with synthetic materialssuch as migration and orientation. Electrospinning also permitsfabrication of oriented fibers to result in structures with inherentanisotropy. These aligned structures can influence cellular growth,morphology and ECM production. For example, Xu et al. found smoothmuscle cell (SMC) alignment with poly(L-lactide-co-ε-caprolactone)fibers [ Xu C. Y., Inai R., Kotaki M., Ramakrishna S., “Alignedbiodegradable nanofibrous structure: a potential for blood vesselengineering”, Biomaterials 2004 (25) 877-86.] and Lee et al. submittedaligned non-biodegradable polyurethane to mechanical stimulation andfound cells cultured on aligned scaffolds produced more ECM than thoseon randomly organized scaffolds [Lee C. H., Shin H. J., Cho I. H., KangY. M. Kim I. A., Park K. D., Shin, J. W., “Nanofiber alignment anddirection of mechanical strain affect the ECM production of human ACLfibroblast”, Biomaterials 2005 (26) 1261-1270].

The process of electrospinning involves placing a polymer-containingfluid (for example, a polymer solution, a polymer suspension, or apolymer melt) in a reservoir equipped with a small orifice, such as aneedle or pipette tip and a metering pump. One electrode of a highvoltage source is also placed in electrical contact with thepolymer-containing fluid or orifice, while the other electrode is placedin electrical contact with a target (typically a collector screen orrotating mandrel). During electrospinning, the polymer-containing fluidis charged by the application of high voltage to the solution or orifice(for example, about 3-15 kV) and then forced through the small orificeby the metering pump that provides steady flow. While thepolymer-containing fluid at the orifice normally would have ahemispherical shape due to surface tension, the application of the highvoltage causes the otherwise hemispherically shaped polymer-containingfluid at the orifice to elongate to form a conical shape known as aTaylor cone. With sufficiently high voltage applied to thepolymer-containing fluid and/or orifice, the repulsive electrostaticforce of the charged polymer-containing fluid overcomes the surfacetension and a charged jet of fluid is ejected from the tip of the Taylorcone and accelerated towards the target, which typically is biasedbetween −2 to −10 kV. Optionally, a focusing ring with an applied bias(for example, 1-10 kV) can be used to direct the trajectory of thecharged jet of polymer-containing fluid. As the charged jet of fluidtravels towards the biased target, it undergoes a complicated whippingand bending motion. If the fluid is a polymer solution or suspension,the solvent typically evaporates during mid-flight, leaving behind apolymer fiber on the biased target. If the fluid is a polymer melt, themolten polymer cools and solidifies in mid-flight and is collected as apolymer fiber on the biased target. As the polymer fibers accumulate onthe biased target, a non-woven, porous mesh is formed on the biasedtarget. Under certain conditions, for instance with solutions lackingsufficient viscosity and/or electrospun with certain tolerances, a fiberis not formed, but a spray is formed, depositing discrete droplets ontothe target instead of a fiber. This is electrospraying.

The properties of the electrospun structures, e.g., elastomericscaffolds, can be tailored by varying the electrospinning conditions.For example, when the biased target is relatively close to the orifice,the resulting electrospun mesh tends to contain unevenly thick fibers,such that some areas of the fiber have a “bead-like” appearance.However, as the biased target is moved further away from the orifice,the fibers of the non-woven mesh tend to be more uniform in thickness.Moreover, the biased target can be moved relative to the orifice. Incertain non-limiting embodiments, the biased target is moved back andforth in a regular, periodic fashion, such that fibers of the non-wovenmesh are substantially parallel to each other. When this is the case,the resulting non-woven mesh may have a higher resistance to strain inthe direction parallel to the fibers, compared to the directionperpendicular to the fibers. In other non-limiting embodiments, thebiased target is moved randomly relative to the orifice, so that theresistance to strain in the plane of the non-woven mesh is isotropic.The target can also be electrospun on a rotating mandrel. In this case,the properties of the non-woven mesh may be changed by varying the speedof rotation. The properties of the electrospun structure may also bevaried by changing the magnitude of the voltages applied to theelectrospinning system. In one non-limiting embodiment, theelectrospinning apparatus includes an orifice biased to 12 kV, a targetbiased to −7 kV, and a focusing ring biased to 3 kV. Moreover, a usefulorifice diameter is 0.047″ (I.D.) and a useful target distance is about23 cm. Other electrospinning conditions that can be varied include, forexample and without limitation, the feed rate of the polymer solutions,the solution concentrations, and the polymer molecular weight.

In certain embodiments, electrospinning is performed using two or morenozzles, wherein each nozzle is a source of a different polymersolution. The nozzles may be biased with different biases or the samebias in order to tailor the physical and chemical properties of theresulting non-woven polymeric mesh. Additionally, many different targetsmay be used. In addition to a flat, plate-like target, use of a mandrelor a revolving disk as a target is contemplated.

When the electrospinning is to be performed using a polymer suspension,the concentration of the polymeric component in the suspension can alsobe varied to modify the physical properties of the elastomeric scaffold.For example, when the polymeric component is present at relatively lowconcentration, the resulting fibers of the electrospun non-woven meshhave a smaller diameter than when the polymeric component is present atrelatively high concentration. Without wishing to be limited by theory,it is believed that lower concentration solutions have a lowerviscosity, leading to faster flow through the orifice to produce thinnerfibers. One skilled in the art can adjust polymer concentrations toobtain fibers of desired characteristics. Useful ranges ofconcentrations for the polymer component are from 1 wt % to 25 wt %, 4wt % to 20 wt %, and from 10 wt % to 15 wt %, including incrementstherebetween for all ranges.

In one non-limiting embodiment, the structure is produced by co-electrospinning a polymer suspension comprising a synthetic polymeric componentand a biological polymeric component, along with electrospraying the ECMgel and/or other liquid. In another non-limiting embodiment, thepolymeric component of the structure is produced by electrospinning apolymer suspension comprising a synthetic polymeric component from onenozzle and a polymer suspension comprising a biological polymericcomponent from another nozzle. Non-limiting examples of useful range ofhigh-voltage to be applied to the polymer suspension is from 0.5 to 30kV, from 5 to 25 kV, and from 10 to 15 kV.

The ECM gel component of the structure is sprayed (e.g. pressuresprayed) or electrosprayed concurrently with the electrospinning of thepolymer(s). Likewise, the liquid component of the wet-electrospunlayer(s) is sprayed or electrosprayed concurrently with the polymericconstituents.

In one embodiment, a multi-layer structure is produced. FIG. 2 depicts athree-layer structure 10. The structure 10 comprises a first layer 20 ofa wet-electrospun biodegradable elastomeric polymer composition,comprising a biodegradable, biocompatible elastomeric polymercomposition and a liquid, such as an aqueous liquid, for example andwithout limitation a liquid selected from one or more of water, aphysiological salt solution, a buffer solution, a mammalian bloodproduct or cell culture medium. The structure 10 comprises a secondlayer 30 attached to the first layer 20, comprising a biodegradableelastomeric polymer composition and an ECM gel. The structure alsocomprises a third layer 40 attached to the second layer 30 opposite thefirst layer 20, comprising a biodegradable elastomeric polymercomposition and a liquid, such as an aqueous liquid, for example andwithout limitation a liquid selected from one or more of water, aphysiological salt solution, a buffer solution, a mammalian bloodproduct or cell culture medium. The first layer 20 and second layer 30are attached at a first interlayer 50 and the second layer 30 and thirdlayer 40 are attached at a second interlayer 60. The first layer 20 andthe third layer 40 may be the same or different, comprising the samebiodegradable elastomeric polymer composition and/or a liquid, such asan aqueous liquid, for example and without limitation a liquid selectedfrom one or more of water, a physiological salt solution, a buffersolution, a mammalian blood product and cell culture medium or differentbiodegradable elastomeric polymer composition and/or a liquid, such asan aqueous liquid, for example and without limitation a liquid selectedfrom one or more of water, a physiological salt solution, a buffersolution, a mammalian blood product and cell culture medium. The secondlayer 30 may comprise the same biodegradable elastomeric polymercomposition as the first layer 20 and/or the third layer 40.

Because the multi-layered structure 10 of FIG. 2 is produced byelectrospinning, the interlayers 50 and 60 comprise fibers of both theadjacent layers, a number of which are interlocked or intertwined, orcan be continuous between layers. In one embodiment, the biodegradableelastomeric polymer composition is deposited continuously from the firstlayer 20 through the third layer 40. While the biodegradable elastomericpolymer composition is deposited continuously, the liquid, such as anaqueous liquid, for example and without limitation a liquid selectedfrom one or more of water, a physiological salt solution, a buffersolution, a mammalian blood product and cell culture medium is firstdeposited, producing the first layer, then the ECM gel is deposited,producing the second layer 30, and lastly the liquid, such as an aqueousliquid, for example and without limitation a liquid selected from one ormore of water, a physiological salt solution, a buffer solution, amammalian blood product and cell culture medium is deposited, producingthe third layer 40. In this embodiment, the biodegradable elastomericpolymer composition is the same throughout the structure 10, and theliquid, such as an aqueous liquid, for example and without limitation aliquid selected from one or more of water, a physiological saltsolution, a buffer solution, a mammalian blood product and cell culturemedium is the same in the first and third layers, 20 and 40. In thisparticular electrospinning process, three reservoirs are used: onecontaining the biodegradable elastomeric polymer composition, onecontaining the liquid, such as an aqueous liquid, for example andwithout limitation a liquid selected from one or more of water, aphysiological salt solution, a buffer solution, a mammalian bloodproduct and cell culture medium, and one containing the ECM gel.Alternately, additional reservoirs can be used in order to change one ormore ingredients in each layer. For example two reservoirs, eachcomprising a different biodegradable elastomeric polymer composition maybe used for deposition of two adjacent layers, and in order to increaseadhesion between layers the first biodegradable elastomeric polymercomposition is deposited followed by the second, with a period of timeduring deposition in which both are deposited, resulting in aninterlayer comprising both biodegradable elastomeric polymercompositions. Flow of materials from the reservoirs may be controlledmanually or by computer.

In one alternate embodiment to that of FIG. 2, the third layer 40 andtherefore the second interlayer 60 are omitted producing a structure oftwo layers. Likewise, additional layers or interlayers may be includedin the structure, yielding a structure of four or more layers.Additional ingredients, such as therapeutic agents or cells as describedherein, can be deposited, e.g., by electro spraying, onto or within oneor more layers.

The multi-layered structure, for example as illustrated in FIG. 2,combines a biodegradable elastomeric polymer composition and an ECM gel,with one or more physically stronger layers of a wet-electrospunbiodegradable elastomeric polymer composition. The wet-electrospunstronger layers have a lower amount of the ECM gel material than thelayer(s) comprising the biodegradable elastomeric polymer compositionand the ECM gel material, and in certain embodiments omit the ECM gelmaterial. As an example, the multi-layered structure comprises a layerof the combined polymer/ECM material between two layers ofwet-electrospun biodegradable elastomeric polymer compositionessentially as shown in FIG. 2. Examples of wet-electrospunbiodegradable elastomeric polymer compositions are described inInternational Patent Application No. PCT/US2011/038332, filed May 27,2011, incorporated herein by reference in its entirety. Suitablebiodegradable elastomeric polymer compositions for wet-electrospinningare described herein as the biodegradable elastomeric polymercomposition described above, which may comprise a biological polymercomponent, though typically not an ECM gel. Therefore according to oneembodiment, a composition is produced comprising a first layer of awet-electrospun biodegradable elastomeric polymer composition, a secondlayer of a biodegradable elastomeric polymer composition co-depositedwith an ECM gel and a third layer on an opposite side of the secondlayer from the first layer of a wet-electrospun biodegradableelastomeric polymer composition that is the same or different than thewet-electrospun biodegradable elastomeric (co)polymer of the firstlayer.

The wet-electrospun layers are “wet electrospun,” meaning a liquid, suchas an aqueous liquid, for example and without limitation a liquidselected from one or more of water, a physiological salt solution, abuffer solution, a mammalian blood product or cell culture medium, suchas a serum-containing liquid or a mammalian blood product, is depositedas the polymer is electrospun. One method would be to spray the liquidat the same time the polymer is electrospun. In one embodiment, theliquid is electrosprayed in substantially the same manner as the polymeris electrospun, the only difference being the deposited liquid is lessviscous than the polymer, and the potential difference is such thatdroplets, rather than fibers are deposited. In one embodiment, theliquid is serum in normal saline, PBS, cell culture medium or a balancedsalt solution, optionally comprising other additives. In the examplebelow, the electrosprayed medium is Dulbecco's Modified Eagle Medium(DMEM) with 10% fetal bovine serum (FBS), 10% horse serum, 1%penicillin/streptomycin, and 0.5% chick embryo extract. As can berecognized by those of ordinary skill in the relevant arts, there are amultitude of salt solutions, buffered salt solutions, media, mediasupplements, active agents, such as antibiotics, growth factors andcytokine, biopolymers and ECM-derived material that would serve equallyas a substitute for the electrosprayed serum-containing liquidsdescribed in the examples below. Compositions that are do not includeblood products are referred to herein as physiological solutions, whichare biocompatible, aqueous solutions, including salt solutions andblood-product-free medium, though blood products can be added to thephysiological solutions. Other potentially useful media include, withoutlimitation: DMEM, MEM, RPMI 1640, F10, OptiMEM, serum-free media, EMEM,EBM-2, F12, IMDM, and Media 199 (available, e.g., from Invitrogen). Saltsolutions may be used instead of media, such as, without limitation:saline, normal saline (approximately 0.9% (w/v)), Dulbecco'sphosphate-buffered salines, Hanks' balanced salt solutions, phosphatebuffered salined or Earle's balanced salt solutions. Media supplementsinclude, without limitation: HEPES, Calcium chloride, or sodiumbicarbonate. Antibiotics include, without limitation: actinomycin D,ampicillin, carbenicillin, cefotaxime, fosmidomycin, gentamycin,kanmycin, neomycin, penicillin streptomycin, polymyxin B andstreptomycin. Mixtures of more than one media, supplement, or antibioticcan also be used.

According to one embodiment, the electrosprayed liquid comprises one ormore xenogeneic, allogeneic, isogeneic, syngeneic or autologous bloodproducts, such as serum, plasma or platelet-rich plasma. “Serum” is acell-free, fibrinogen-free blood fraction. In one non-limitingembodiment, an aliquot of a patient's blood is removed and serum isprepared from the blood by allowing the blood to clot and removing theclotted material and cellular material, typically by first “ringing” thesample, and then by centrifugation. Plasma is made by centrifuging atube of fresh blood containing an anti-coagulant in a centrifuge untilthe blood cells fall to the bottom of the tube. Platelet Rich Plasma isdefined as a volume of the plasma fraction of autologous blood having aplatelet concentration above baseline. (See, generally, Sampson et al.Curr Rev Musculoskelet Med. 2008 December; 1(3-4):165-74). One method ofpreparing platelet-rich plasma is by density-gradient centrifugation andcollection of the buffy coat. A device, such as the Biomet BiologicsGPS® III device can be used to obtain a platelet rich plasma fraction.Platelet-rich buffy coat preparations can be mixed with plasma, serum,saline, PBS or any suitable salt, buffer, media, etc.

For either the wet-electrospun layer(s) or the ECM gel-containinglayers, stabilizing compositions, such as stabilizing proteins may beincluded in the electrosprayed liquid composition. Likewise viscosityenhancers, including, without limitation: polymeric compounds may alsobe added.

Allogeneic blood fractions, such as one or more of serum, plasma orplatelet-rich plasma, may be used. An electrospray liquid to beconcurrently electrosprayed during electrospinning of the polymercomponent of the matrices described herein may comprise blood fraction(e.g., serum, plasma or platelet-rich plasma, or mixtures thereof)concentrations ranging from approximately 1% to 100%, including anyincrement therebetween, such as 1%, 5%, 10%, 20%, 30%, 40%, 50%, 60%,70%, 80%, 90% and 100% and any increment therebetween. In oneembodiment, the electrospray liquid comprises from 5%-25% autologous orallogeneic blood product(s), and in another embodiment, 20%. When theblood fraction(s) is not 100% of the electrospray liquid, theelectrospray liquid will comprise a suitable aqueous liquid, such aswater, normal saline, PBS, or a cell culture medium as described above.As described elsewhere herein, the electrospray liquid also may compriseantibiotics, buffers, active agents, growth factors, cytokines,biopolymers, ECM derived material etc. in appropriate concentrations.

Because the electrospinning process may be controlled either manually orby computer, different ratios of polymer and electrosprayed liquid maybe deposited in different layers of the matrix. For example, the ratioof liquid to polymer may increase in regions of the matrix where it isdesirable to get increased cell infiltration, though too much liquidcould lead to polymer delamination.

The materials made by the methods described herein may be sterilized byany useful means, and then packaged and distributed, e.g., according tostandard usage in the biomedical industry. In use, the structuresdescribed herein can be used for cell growth and implantation for tissuegeneration or regeneration. For example, sheets of the structures can beused to replace skin or abdominal wall tissue. The sheets can besutured, glued or otherwise affixed into place. Because the structuresbiodegradable, it is gradually replaced by native-origin tissue. Ifformed into a tubular structure, it may be used to replace blood vesselsor portions of a patient's digestive tract and implanted, e.g., byanastomosis. It can also be used as a reinforcement for tissue alreadypresent in the patient. As seen herein, damage to an abdominal wall canbe repaired by suturing the scaffold into remaining abdominal walltissue, preferably to completely replace abdominal wall tissue removedor damaged. The scaffolds also may be used in vitro, in any suitablecell growth vessel, bioreactor, plate, flask, etc. In one embodiment,prior to implantation, the scaffold is placed in a cell culture vesselwith media and cells of a patient, and the cells are allowed to grow on,and infiltrate within the scaffold prior to implantation. In anotherembodiment, the scaffold is placed within a patient and after a desiredperiod of time for cell infiltration, explanted and re-implanted at adifferent location.

In another embodiment, the cells of interest are dissolved into anappropriate solution (e.g., a growth medium, buffer, or even the ECM gelelectrosprayed during formation of the scaffold) and then sprayed onto abiodegradable elastomeric scaffold while the scaffold is being formed byelectrospinning. This method is particularly suitable when a highlycellularized tissue engineered construct is desired. While pressurespraying (that is, spraying cells from a nozzle under pressure) iscontemplated herein, in certain non-limiting embodiments, the cells areelectrosprayed onto the non-woven mesh during electrospinning. Asdescribed herein, electrospraying involves subjecting a cell-containingsolution with an appropriate viscosity and concentration to an electricfield sufficient to produce a spray of small charged droplets ofsolution that contain cells.

EXAMPLES

The objective of these studies is to identify a biomaterial for use indevelopment of a biohybrid device combining the biomechanical propertiesof synthetic scaffold materials with the biochemical features of naturalacellular scaffold devices. These materials will find use inreconstruction of tissues and structures that require good physicalstrength, such as in pelvic floor or abdominal wall replacement. Thisrequires analysis of: mechanical properties of the biomaterials; invitro and in vivo biocompatibility of the materials; and in vivo hostresponse evaluation in a rodent model.

The biodegradable thermoplastic elastomer poly(ester urethane) urea(PEUU), prepared essentially as described by co-polymerization ofpolycaprolactone diol (Mw 2000) and 1,4-diisocyanobutane at 70° in thepresence of Sn(OCt)₂ (stannous octoate or Tin 2-Ethylhexanoate) toproduce a prepolymer and then reacting the prepolymer with putrescine(H₂N(CH₂)₄NH₂) (Guan J J, et al. Synthesis, characterization, andcytocompatibility of elastomeric, biodegradablepoly(ester-urethane)ureas based on poly(caprolactone) and putrescine. JBiomed Mater Res. 2002; 61:493-503).

Dermal ECM gel is prepared from porcine dermis as follows. Frozensamples of porcine dermis were thawed at room temperature and cut intosmaller sized pieces. The tissue samples were subject to a series ofwashes for enzymatic decellularization (trypsin washes), osmotic lysis(dH₂O washes), sterilization (ethanol), peroxide washes, aqueous washes(1% Triton X-100 in EDTA/Trizma), disinfection (peracetic acid), andfinal aqueous washes. Acellular samples were lyophilized and comminutedinto powder form. Powdered dECM was subject to enzymatic digest (pepsin)for 48 hours. dECM digest solutions are adjusted in concentration andosmotic strength to yield a working gelling solution of neutral pH at 10mg/ml and used immediately for the preparation of PEUU/dECM biohybriddevices by co-electrospinning.

Electrospinning is conducted either onto a non-rotating surface or ontoa spinning mandrel, as described above. FIG. 3 depicts mechanicalproperties of PEUU by itself prepared either as a film, a TIPS scaffoldor electrospun. Table A provides additional physical properties of thosematerials.

TABLE A Tensile Strength Breaking Strain Polymer Processing (mPa) (%)PEUU Film 27 ± 4 820 ± 70 PEUU TIPS  1.5 ± .02 200 ± 60 PEUU Electrospun13 ± 4 220 ± 80

Scaffolds manufactured from PEUU and solubilized UBM, andpost-implantation histology of those scaffolds may be preparedessentially as described in Stankus et al., Hybrid nanofibrous scaffoldsfrom electrospinning of a synthetic biodegradable elastomer and urinarybladder matrix, J Biomater. Sci. Polym. Ed. (2008) 19(5):635-652, thatis by blending PEUU and ECM material an electrospinning in a singlestream. While that process is effective to some extent for certainpurposes, scaffolds prepared in that manner are not optimal.

The scaffolds prepared according to the methods described herein aresuperior because they combine the benefits of two excellent scaffoldmaterials to yield a much superior product. Electrospun elastomericscaffolds have the benefit of elasticity, biodegradation, goodmechanical behavior (e.g., surgical handling) and controllablemechanical properties, but negatives include poor cellular infiltrationand, depending on the polymer composition, foreign body response priorto complete degradation. Dermal ECM hydrogels have the benefit of goodbiocompatibility and cell and tissue chemoattraction, but negativesinclude weak mechanical properties, poor control of mechanicalproperties and fast degradation. The benefits of the combinedpolymer/ECM gel material include: superior tissue mimetic, goodbiodegradation rates, elasticity, good cellular infiltration, adequateto excellent mechanical support and adequate to good surgical handling.

In the experiments described below, the polymer/ECM gel is formed byelectrospinning PEUU as described above, onto a spinning mandrel andconcurrently electrospraying dermal ECM onto the scaffold, as describedbelow. Once formed, the scaffold is cut off the mandrel and heated to37° C. to cause the ECM material to gel.

Example 1

A hybrid scaffold (PEUU/dECM=50/50) was prepared from PEUU, prepared asdescribed above and dermal ECM (dECM) prepared as described above. Thescaffolds were formed by concurrent electrospinning of the PEUU andelectrospraying of the dECM material. 10 mL dermal ECM gel solution (10mg/ml) was fed by a syringe pump at 1.5 mL/min into a sterilizedcapillary (1.2 mm inner diameter) charged at 7 kV and suspended 4 cmabove the target mandrel (19 mm diameter). Concurrently, PEUU inhexafluoroisopropanol solution (10%, w/v) was fed at 10 mL/h from acapillary, charged at 12 kV and perpendicularly located 20 cm from thetarget mandrel. The mandrel was charged at −4 kV and rotated at 250 rpm(8 cm/s tangential velocity) while translating back and forth 8 cm alongthe x-axis at 0.15 cm/s. After processing, PEUU/gel solution hybrid wascut off from mandrel using a blade and then was immediately placed in anincubator at 37° C. After 2 h, dECM gel solution completely formed asolid gel and PEUU/dECM gel hybrid scaffold was obtained.

FIG. 4 shows cross-section morphology of the PEUU/dECM hybrid scaffold(50:50). FIG. 5 shows surface morphology of the PEUU/dECM hybridscaffold (50:50). It was observed that the fiber/gel microstructure ofPEUU/dECM gel hybrid scaffold forms a multilammelar structure withfibers extending between the layers. The resultant material is easilyhandled and is elastic. FIGS. 6A and 6B provide graphs showingmechanical properties of PEUU/dECM hybrid scaffolds at differentPEUU/dECM ratios, which were tuned by changing gel feeding rate.

10 mL dermal ECM gel solution (10 mg/ml) was fed by a syringe pump at 1,1.5 or 2 mL/min into a sterilized capillary (1.2 mm inner diameter)charged at 7 kV and suspended 4 cm above the target mandrel (19 mmdiameter). Concurrently, PEUU in hexafluoroisopropanol solution (12%,w/v) was fed at 20 mL/h from a capillary, charged at 12 kV andperpendicularly located 20 cm from the target mandrel. The mandrel wascharged at −4 kV and rotated at 250 rpm (8 cm/s tangential velocity)while translating back and forth 8 cm along the x-axis at 0.15 cm/s.After processing, PEUU/gel solution hybrid was cut off from mandrelusing a blade and then was immediately placed in an incubator at 37° C.After 2 h, dECM gel solution completely formed a solid gel. Threedifferent hybrid scaffolds at PEUU/dECM ratios of 80/20, 72/28, and67/33 were obtained when gel solution feeding rates were 1, 1.5 and 2ml/min, respectively.

A strip sample was cut from PEUU/dECM hybrid scaffold at longitudinal orcircumferential direction. Uniaxial mechanical properties of such samplewere measured on an MTS Tytron 250 MicroForce Testing Workstation atroom temperature. The crosshead speed was set at 1 inch/min according toASTM D638-98. FIG. 7 depicts typical stress-strain curves of PEUU/dECMgel hybrid scaffold (80/20) at longitudinal and circumferentialdirections.

Example 2

A PEUU/dECM hybrid scaffold (50/50) was prepared and tested in a partialthickness defect model in the rat (Valentin J E et al. J Bone Jt Surg Am88 (2006), pp. 2673-2686; Brown B N et al. Biomaterials 30 (2008), pp.1482-1491; Valentin J E et al. Biomaterials. 2010; 31(29):7475-7484).Briefly, a 1.0×1.0 cm lateral defect in muscle is used. Material (e.g.,a biologic scaffold), replaces the outermost muscle layers (inner andouter obliques), while leaving in place the inner muscle layers(transversalis m.) and peritoneum. The material is attached using foursutures, one at each corner for demarcation and transfer of mechanicalload. This model allows evaluation of biological integration as well asimmune response to materials, and minimizes the effects of suturingmaterials. Scaffolds were prepared from electrospun PEUU, alone, asdescribed above and 50-50 PEUU/dECM as described above. Scaffolds wereimplanted in a total of four rats, with one rat for each time point.FIG. 8 shows macroscopic images of both implants at two and four weekspost-implant. FIGS. 9A and 9B show photomicrographs (H&E stains) of twoPEUU sections at two and four weeks, respectively. FIGS. 10A and 10Bshow photomicrographs (H&E stains) of two PEUU/dECM (50-50) sections attwo and four weeks, respectively. In FIGS. 9A, 9B, 10A and 10B, theright and left images are from different areas of the implant in asingle rat. Cellular infiltration and tissue remodeling appearsignificantly improved with the incorporation of the ECM gel into thescaffold.

A full-thickness animal model also was used for testing the scaffolds inrats. This tests the biomechanical properties of the scaffold, as thedefect requires replacement of a higher amount of connective tissue thanin the first, lateral partial defect model described above. A 1.0×2.5 cmdefect is made on the animal's midline, with matched size replacement(˜3-4 mm thick). The scaffold material replaces all muscle layers andperitoneum and is held in place using continuous sutures. This modelfacilitates evaluation of devices with focus on biomechanicalproperties. In this model a higher amount of connective tissue isreplaced as compared to the lateral partial defect model.

In this experiment, two rats were implanted with PEUU/dECM gel 50/50hybrid scaffold. PEUU and dECM alone were implanted into rats ascontrols. At four weeks post implantation, vasculature was seen on theperitoneal side of the repair to some degree in all samples (PEUU, dECMor PEUU/dECM), but significantly more when the blended material wasused. The PEUU/dECM expanded circumferentially (transversely), while noapparent change in longitudinal length was seen. FIGS. 11A and 11B showMasson's Trichrome staining of the rats body wall treated with either aPEUU device or a device of acellular dECM at two and four weeks. ThePEUU group showed a very limited level of cellular infiltration into thedevice. The dECM-treated group showed a significantly level of cellularinfiltration into the entire device. FIGS. 12A and 12B showphotomicrographs of an H&E stain of a rat abdominal wall cross-sectionrepaired using PEUU/dECM 50/50 hybrid scaffold. This shows good tissueinfiltration. FIG. 13 shows biaxial stress-stretch curves of nativeabdominal wall tissue and for PEUU/dECM 50/50 hybrid scaffoldspre-implant and 4 weeks post-implant. The test curves were generated asdescribed above.

Example 3

A patch material of PEUU/dECM 72/28 was prepared as described above. ThePEUU was electrospun and the dECM gel was electrosprayed essentially asdescribed above, and a dry polymer ratio of 72% PEUU and 28% dECM. 10 mLdermal ECM gel solution (10 mg/ml) was fed by a syringe pump at 1.5mL/min into a sterilized capillary (1.2 mm inner diameter) charged at 7kV and suspended 4 cm above the target mandrel (19 mm diameter).Concurrently, PEUU in hexafluoroisopropanol solution (12%, w/v) was fedat 20 mL/h from a capillary, charged at 12 kV and perpendicularlylocated 20 cm from the target mandrel. The mandrel was charged at −4 kVand rotated at 250 rpm (8 cm/s tangential velocity) while translatingback and forth 8 cm along the x-axis at 0.15 cm/s. After processing,PEUU/gel solution hybrid was cut off from mandrel using a blade and thenwas immediately placed in an incubator at 37° C. After 2 h, dECM gelsolution completely formed a solid gel and a PEUU/dECM 72/28 scaffoldwas obtained.

The patch was prepared as described above and implanted into two ratswith an endpoint of 2 and 4 weeks. FIGS. 14A and 14B arephotomicrographs of H&E stained cross sections of the PEUU/dECM 72/28hybrid implant at two and four weeks, respectively, with left and rightpanels showing the microscopic results obtained in both animalsimplanted. FIG. 15 shows biaxial stress-stretch curves of nativeabdominal wall tissue and for PEUU/dECM 50/50 hybrid scaffoldspre-implant, 2 and 4 weeks post-implant.

In sum, in the transition from the first to second generation materials,the amount of PEUU was increased with respect to the amount of dECM inthe patch. In future trials, the flow rates of the PEUU and dECM duringco-integration into the matrix may be altered to reduce solventincorporation and change fiber diameter. Different compositions and flowrates at different times can produce different lamellar formulationsthat may prove beneficial. In a preliminary study, FIG. 16 shows theinfluence of processing parameters on mechanics of a pre-implantationpatch. In FIG. 16, the number in bracket is the process condition of thePEUU solution infusion rate (ml/h) to dermal ECM solution infuse rate(ml/min). Slowing the polymer infusion rate generally leads to thinnerfibers (higher density).

With respect PEUU/dECM [50/50] hybrid, there was a problem withreproducibility. There was a delamination effect in the sample used forpartial defect repair, but not in sample used in full thickness model.The device was too weak (suture retention), high levels of cellinfiltration, neotis sue formation were seen in the PEUU/dECM gelbiohybrid but not in PEUU alone, and a visible inflammatory response isseen, with multinucleated giant cells.

The materials having a higher ratio of PEUU to dECM (PEUU/dECM 72/28)exhibit improved strength as compared to the 50/50 hybrid, high levelsof cellular infiltration, neotissue formation and remodeling to achievemechanical properties comparable to native abdominal wall.

Even with these materials, though significant improvements over the50/50 material, initial strength could be improved. Longer term resultsare planned, as is investigation of M1/M2 markers in vitro and in vivo.

Example 4

A severe abdominal wall defect due to laparotomy after abdominalcompartment syndrome or severe abdominal injury remains a challengingproblem for surgeons. Primary closure is difficult because of the riskof abdominal hyper pressure or intraabdominal infection. The standardtreatment includes open treatment followed by secondary abdominal wallreconstruction. Many techniques utilizing autologous tissue orprosthetic materials have been applied to reconstruct full abdominalwall defects. But disadvantages for such two materials arecomplications, tissue adhesion, infections and hernia recurrence. Here,we designed a biohybrid composite material that offers both strength andbioactivity for optimal healing towards native tissue behavior. Thismaterial, which has top and bottom layers of polymer fibers and a middlelayer of polymer fibers and extracellular matrix gel biohybrid, wasfabricated using a sandwich technique, which includes wetelectrospinning for the beginning and end of the processing, and gelelectrospray/polymer electrospinning for the middle of processing. Theresultant sandwich scaffold possessed attractive mechanical propertiesand anisotropic behavior mimicking native abdominal wall as well as goodbioactivity for tissue ingrowth and remodeling. By creating apolymer-rich upper and lower surface the composite scaffold provideslonger lasting structural elements that also provide good suturability.The ECM-rich interior provides a bioactive pathway for cell migrationand accelerated healing. The fibers within the interior region providestructural connectivity to the rest of the scaffold and improve themechanical properties. The biohybrid scaffold would find opportunitiesin the clinical applications for abdominal wall reconstruction, pelvicfloor repair, breast reconstruction, as well as other soft tissuerepairs.

The PEUU/dECM material (PEUU/dECM 72/28) described above was sandwichedbetween two layers of wet-electrospun PEUU. The material was prepared bycontinuous electrospinning on a mandrel of a PEUU solution andconcurrently electrospraying first PBS (phosphate-buffered saline),followed by dECM solution described above, and followed by PBS.

In further detail, the PEUU, as described above, was electrospun and thedECM gel was electrosprayed essentially as described above, and a drypolymer ratio of 72% PEUU and 28% dECM. PEUU in hexafluoroisopropanolsolution (12%, w/v) was fed at 20 mL/h from a capillary, charged at 12kV and perpendicularly located 20 cm from the target mandrel.Concurrently, PBS and dECM was electrosprayed in the following order.First, PBS was fed by a syringe pump at 0.2 mL/min into a sterilizedcapillary (1.2 mm inner diameter) charged at 7 kV and suspended 4 cmabove the target mandrel (19 mm diameter). Second, 10 mL dermal ECM gelsolution (10 mg/ml) was fed by a syringe pump at 1.5 mL/min into asterilized capillary (1.2 mm inner diameter) charged at 7 kV andsuspended 4 cm above the target mandrel (19 mm diameter). Third, PBS wasfed by a syringe pump at 0.2 mL/min into a sterilized capillary (1.2 mminner diameter) charged at 7 kV and suspended 4 cm above the targetmandrel (19 mm diameter). The mandrel was charged at −4 kV and rotatedat 250 rpm (8 cm/s tangential velocity) while translating back and forth8 cm along the x-axis at 0.15 cm/s. Three different electrospinningdurations, 10 minutesm, 20 minutes and 30 minutes were tested. Afterprocessing, the three-layer structure was cut off from the mandrel usinga blade and then was immediately placed in an incubator at 37° C. After2 h, dECM gel solution completely formed a solid gel and a hybridcomposite structure was obtained, essentially as depicted in FIG. 2.

FIG. 17 are photomicrographs showing cross sections of the compositestructure prepared by this method.

FIG. 18 are photomicrographs of Masson's trichrome stainedcross-sections of the sandwiched sheets, for the three differentelectrospinning durations.

FIG. 19 is a photomicrograph of Masson's trichrome stainedcross-sections of the sandwiched sheets (20 minute electrospinningduration). This figure shows polymer fibers within the dECM gel region.

FIGS. 20A and 20B are graphs showing stress (FIG. 20B) and strain (FIG.20B) values for the three composite structures prepared according to themethods described in the present example, as compared to PEUU/dECM(72/28) prepared as described above.

FIG. 21 are graphs providing comparisons of biaxial mechanical testingfor the sandwich composite (20 minutes), PEUU/dECM material, nativeabdominal wall muscle tissue (rat) and a Dacron/dECM gel biohybrid(non-degradable). Constructs were tested under equal biaxial tension. Ofnote the PEUU/dECM gel biohybrid (72:28) mechanically failed above 50kPa.

The sandwich structure was implanted into rat abdominal wall essentiallyas described above (full thickness), along with a control PEUU/dECM(72:28). After three weeks, the material was explanted and analyzed.FIG. 22 provides photomicrographs showing H&E and Masson's trichromestains of that explanted tissue.

FIG. 23 are graphs providing comparisons of biaxial mechanical testingfor the explanted sandwich composite, explanted PEUU/dECM material, andnative abdominal wall muscle tissue at four and eight weekspost-implant. The tissue explanted from the sandwich structure groupshows excellent and unexpected similarity to native muscle tissue.

One of the goals of preparing the sandwiched composite structure is toimprove suturability as compared to PEUU/dECM (72:28) material. Sutureretention strength was therefore measured for the sandwiched material ascompared to the PEUU/dECM (72:28) material. FIG. 24 is a graph showingsuture retention strength of sandwich scaffold tuning bywet-electrospinning time, indicating the superiority of the sandwichedmaterial as compared to the PEUU/dECM (72:28) material.

Having described this invention above, it will be understood to those ofordinary skill in the art that the same can be performed within a wideand equivalent range of conditions, formulations and other parameterswithout affecting the scope of the invention or any embodiment thereof.

We claim:
 1. A biohybrid scaffold comprising a matrix of abiodegradable, biocompatible elastomeric polymer and an ECM-derived gelinterspersed substantially evenly throughout the matrix.
 2. Thebiohybrid scaffold of claim 1, wherein the ECM-derived gel has a lowercritical solution temperature (LCST) of less than 37° C.
 3. Thebiohybrid scaffold of claim 2, wherein the ECM-derived gel has an LCSTof from 20° C. to less than 37° C.
 4. The biohybrid scaffold of claim 1,wherein the ECM-derived gel composition is prepared by: (i) solubilizingdecellularized tissue that has not been dialyzed by digestion with anacid protease, thereby producing a digest solution; and (ii) raising thepH of the digest solution to between 7.2 and 7.8.
 5. The biohybridscaffold of claim 1, wherein the biodegradable, biocompatibleelastomeric polymer comprises a poly(ester urethane) urea (PEUU), apoly(ether ester urethane)urea (PEEUU), a poly(ester carbonate)urethaneurea (PECUU), and/or a poly(carbonate)urethane urea (PCUU).
 6. Thebiohybrid scaffold of claim 1, in which the biodegradable, biocompatibleelastomeric polymer comprises a copolymer of polycaprolactone (Mw˜2000),1,4-diisocyanobutane and putrescine.
 7. The biohybrid scaffold of claim1, further comprising one or more layers of a wet-electrospunbiodegradable, biocompatible elastomeric polymer attached to the matrixof a biodegradable, biocompatible elastomeric polymer and theECM-derived gel interspersed substantially evenly throughout the matrix,forming a composite scaffold structure.
 8. The biohybrid scaffold ofclaim 7, wherein the composite scaffold comprises the matrix of abiodegradable, biocompatible elastomeric polymer and an ECM-derived gelinterspersed substantially evenly throughout the matrix sandwichedbetween two layers of the wet-electrospun biodegradable, biocompatibleelastomeric polymer.
 9. The biohybrid scaffold of claim 7, wherein thewet-electrospun biodegradable, biocompatible elastomeric polymercomprises a PEUU and PBS.
 10. The biohybrid scaffold of claim 7, inwhich polymer fibers between the one or more layers of a wet-electrospunbiodegradable, biocompatible elastomeric polymer and the matrix of abiodegradable, biocompatible elastomeric polymer and the ECM-derived gelinterspersed substantially evenly throughout the matrix are interlockedor continuous between the layers.
 11. A method of growing tissue in apatient comprising implanting the biohybrid scaffold of any one ofclaims 1-10 in a patient at a site of injury or defect in the patient.12. The method of claim 11, wherein the ECM-derived gel composition isprepared by: (i) solubilizing decellularized tissue that has not beendialyzed by digestion with an acid protease, thereby producing a digestsolution; and (ii) raising the pH of the digest solution to between 7.2and 7.8.
 13. The method of claim 11, wherein the biohybrid scaffold isimplanted to repair a soft-tissue injury or defect in a patient.
 14. Themethod of claim 13, wherein the biohybrid scaffold is implanted in theabdominal wall, the pelvic floor, or a breast of a patient, therebyrepairing an injury or defect in the patient.
 15. The method of claim13, wherein the biohybrid scaffold is implanted in an abdominal wall thepatient, thereby repairing an injury or defect in the abdominal wall ofthe patient.